CN104068914A - Fluid ejection device and medical apparatus - Google Patents
Fluid ejection device and medical apparatus Download PDFInfo
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- CN104068914A CN104068914A CN201410120713.1A CN201410120713A CN104068914A CN 104068914 A CN104068914 A CN 104068914A CN 201410120713 A CN201410120713 A CN 201410120713A CN 104068914 A CN104068914 A CN 104068914A
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/32—Surgical cutting instruments
- A61B17/3203—Fluid jet cutting instruments
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00017—Electrical control of surgical instruments
- A61B2017/00137—Details of operation mode
- A61B2017/00154—Details of operation mode pulsed
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
- A61B2560/02—Operational features
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Abstract
A fluid ejection device (100) which ejects a fluid includes an ejection tube (20) which ejects the fluid; a fluid chamber (42) which communicates with the ejection tube (20); a piezoelectric element (30) capable of changing a volume of the fluid chamber (42); a controller (16) which controls a drive voltage applied to the piezoelectric element (30); and a fluid supplying unit (12) which supplies the fluid to the fluid chamber (42) at a predetermined flow rate. If a maximum frequency available to be set of the drive voltage is fmax [Hz] and an amount of change in the volume of the fluid chamber when a maximum value available to be set of the drive voltage is applied to the piezoelectric element (30) to drive the piezoelectric element is V1 [ml], the fluid supplying unit (12) supplies the fluid at the predetermined flow rate above V1fmax [ml/s].
Description
Technical field
The armarium that the present invention relates to fluid ejection apparatus and use this fluid ejection apparatus.
Background technology
The armarium for the treatment of as the fluid contact affected part bio-tissue that makes to eject, known have a fluid ejection apparatus of describing in patent documentation 1 for example.The fluid ejection apparatus of describing in patent documentation 1 is made the volume gain of fluid chamber or is reduced by driving pressure electric device, thereby from playpipe, ejects pulsating flow (stream of pulses).
Because fluid ejection apparatus can be used as for example therapeutic medical scalpel, therefore, require to have stable use sense.And requirement can suppress due to the not enough situation that causes not spraying suitable pulsating flow of fluid of supplying with fluid ejection apparatus.In addition, also requirement can suppress because affected part is supplied to the phenomenon that fluid retention appears in fluid superfluous in fluid ejection apparatus.
In addition, the fluid ejection apparatus of original technology needs less size, lower cost, economizes on resources, is easy to manufacture, improve workability etc.
Prior art document
Patent documentation
Patent documentation 1: JP 2008-82202
Summary of the invention
In view of there being the problems referred to above, the present invention in the following way, can solve at least a portion in above-mentioned problem.
(1), according to a mode of the present invention, the invention provides a kind of fluid ejection apparatus of jet fluid.This fluid ejection apparatus comprises: spray above-mentioned fluid playpipe, be communicated to above-mentioned playpipe fluid chamber, with the flow stipulated to above-mentioned fluid chamber supply with above-mentioned fluid fluid supply unit, make the pulsation generating unit that the fluid in above-mentioned fluid chamber ejects from above-mentioned playpipe, the control part of controlling the action of above-mentioned pulsation generating unit and fluid periodically being ejected from above-mentioned playpipe, the peak frequency of above-mentioned control part jet fluid is fmax(Hz).
When above-mentioned control part makes the action of above-mentioned pulsation generating unit, the variable quantity of the volume of above-mentioned fluid chamber is V1(ml) situation under, above-mentioned fluid supply unit is by surpass V1 * fmax(ml/s) afore mentioned rules flow above-mentioned fluid is provided.According to the fluid ejection apparatus of which, in the fluid deficiency in can the fluid chamber when suppress driving pulsation generating unit, with the flow of stipulating, provide fluid, therefore, and the stability of flow of the fluid ejecting from playpipe, thus can realize stable use sense.
(2), in the fluid ejection apparatus of aforesaid way, above-mentioned fluid supply unit can be with not enough V1 * 2.0 * fmax(ml/s) afore mentioned rules flow above-mentioned fluid is provided.According to the fluid ejection apparatus of this mode, can suppress superfluous fluid and be provided for fluid chamber.
(3) in the fluid ejection apparatus of aforesaid way, as V1(ml) fluid of volume is when ejected from above-mentioned injection peristome by the once driving of above-mentioned pulsation generating unit, when due to the inertia effect of fluid with V1(ml) fluid volume that ejects from above-mentioned injection peristome together with the above-mentioned fluid of volume is V2(ml) time, above-mentioned fluid supply unit can be to surpass (V1+V2) * fmax(ml/s) afore mentioned rules flow above-mentioned fluid is provided.According to this fluid ejection apparatus, Ke Xiang fluid chamber provides the fluid of the desired flow of the inertia effect of having considered fluid.
(4), in the fluid ejection apparatus of aforesaid way, above-mentioned V2 can be also V1 * 0.007.According to the fluid ejection apparatus of this mode, Ke Xiang fluid chamber provides the fluid of the desired flow of the inertia effect of having considered fluid.
(5) a kind of armarium that uses the fluid ejection apparatus of aforesaid way.According to this mode, can provide the armarium that reliability is high.
The multiple element that each mode of the invention described above has is not all necessary, for part or all in addressing the above problem, or, in order to realize part or all in the effect that this description records, a part of element to above-mentioned multiple element, can suitably change, deletes, switch with other new element and delete a part that limits content.And, for part or all in addressing the above problem, or, in order to realize part or all in the effect that this description records, also part or all of the technical characterictic comprising in the alternate manner of part or all and the invention described above of the technical characterictic comprising in a mode of the invention described above can be combined, as independently a kind of mode of the present invention.
For example, a mode of the present invention can be implemented as the device of the more than one key element in 5 key elements such as comprising playpipe, fluid chamber, piezoelectric element, control part, fluid supply unit., this device both can have playpipe, also can not have playpipe.And device both can have fluid chamber, also can there is no fluid chamber.And device both can have piezoelectric element, also can there is no piezoelectric element.And device both can have control part, also can there is no control part.And device both can have fluid supply unit, also can there is no fluid supply unit.Playpipe for example can be constituted as the playpipe with the peristome that sprays above-mentioned fluid.Fluid chamber for example can be constituted as the fluid chamber that is communicated to above-mentioned playpipe.Piezoelectric element for example can be constituted as the piezoelectric element of the volume-variation that can make above-mentioned fluid chamber.Control part for example can be constituted as controls the control part that above-mentioned piezoelectric element is applied to driving voltage.Fluid supply unit for example can be constituted as and with regulation flow, above-mentioned fluid chamber be provided the fluid supply unit of above-mentioned fluid.Particularly, in fluid supply unit, the peak frequency of above-mentioned driving voltage is fmax(Hz), the variable quantity of the volume of the above-mentioned fluid chamber when above-mentioned piezoelectric element being applied to the maximum of above-mentioned driving voltage and above-mentioned piezoelectric element is driven is V1(ml) time, fluid supply unit can be constituted as to surpass V1 * fmax(ml/s) afore mentioned rules flow the fluid supply unit of above-mentioned fluid is provided.This device can be realized as for example fluid ejection apparatus of jet fluid, also can realize as other device beyond the fluid ejection apparatus of jet fluid.According to this mode, can solving device less, cost is lower, economize on resources, be easy to manufacture, improve at least one problem in the variety of issues such as workability.Spray part or all in the technical characterictic of variety of way of fluid ejection apparatus of above-mentioned fluid, all applicable to this device.
The present invention also can realize by the variety of way beyond device.For example, can realize with the method for jet fluid or the modes such as manufacture method of fluid ejection apparatus.
Accompanying drawing explanation
Fig. 1 is the key diagram illustrating as the formation of the fluid ejection apparatus of one embodiment of the present invention.
Fig. 2 is the sectional view after a part that the inside of handpiece forms is shown amplifies.
Fig. 3 is the key diagram that an example of the waveform that is applied to the driving voltage on piezoelectric element is shown.
Fig. 4 is the key diagram that the corresponding relation between the waveform of driving voltage and the state of the distortion of barrier film is shown.
(A) of Fig. 5, (B) of Fig. 5 are the key diagrams of variation of the volume of schematically illustrated fluid chamber.
Fig. 6 is the key diagram of the state of the schematically illustrated fluid that ejects the amount that is greater than excluded volume from fluid jet pipe.
Fig. 7 be illustrate pulsating flow spray moment chronophotograph key diagram.
The specific embodiment
Below, the order according to embodiment, experimental example and variation, describes embodiments of the present invention.
A. embodiment:
Fig. 1 is the key diagram illustrating as the formation of the fluid ejection apparatus 100 of one embodiment of the present invention.
The fluid ejection apparatus 100 of present embodiment is the armarium that is used to medical institutions, by the bio-tissue jet fluid of the affected part to as patient, and has the effect as the scalpel that affected part incision or excision etc. are treated.
Fluid ejection apparatus 100 comprises fluid container 10, fluid supply mechanism 12, handpiece 14, control part 16 and foot switch 18.Between fluid container 10 and fluid supply mechanism 12, by connection tube 19a, connect, between fluid supply mechanism 12 and handpiece 14, by connection tube 19b, connect.In present embodiment, connection tube 19a, 19b are by resin formation.
In fluid container 10, accommodate normal saline as the fluid that offers handpiece 14.Yet, as substituting of normal saline, even if also can hold in fluid container 10 such as pure water or medicinal liquid etc., be injected on bio-tissue other also harmless fluid.
Fluid supply mechanism 12, by connection tube 19a, 19b, is supplied with handpiece 14 by the fluid holding in fluid container 10.Present embodiment is used pump as fluid supply mechanism 12.And as described later, in present embodiment, fluid supply mechanism 12 provides fluid to handpiece 14 with the flow of regulation.
Handpiece 14 is by the utensil of operative doctor hand-held, comprising: fluid jet pipe 20, pulsation generating unit 22, casing 24 and condition switching part 26.Fluid is supplied with pulsation generating unit 22 by connection tube 19b.When applying cable 17a to pulsation generating unit 22 while applying driving voltage by control part 16 by voltage, pulsation generating unit 17a applies pulsation to supplied with fluid.The fluid that has been applied in pulsation goes out from the peristome 20a high velocity jet of the front end of fluid jet pipe 20.Operative doctor by being applied in of ejecting from handpiece 14 fluid of pulsation aim at the bio-tissue as patient's affected part, can carry out treatments such as the incision of affected part or excision.In addition, in following content, also the fluid that has been applied in pulsation is called to pulsating flow or stream of pulses.
Condition switching part 26 is that operative doctor is for switching the size of driving voltage and the operating portion of frequency that pulsation generating unit 22 is applied.Present embodiment adopts dial type selecting arrangement as condition switching part 26, and operative doctor is from size and the frequency of the driving voltage subscribed, selects size and the frequency of the driving voltage that is used for the treatment of.
When the size of driving voltage changes, the size of pulsating flow and the force and velocity of a current (strength) can change; When the frequency shift of driving voltage, the occurrence frequency of pulsating flow also can change.In present embodiment, the size of the driving voltage that can set is as follows with the frequency of the driving voltage that can set:
The size of the driving voltage that can set: 0V～100V
The frequency of the driving voltage that can set: 100Hz～400Hz
, in present embodiment, the maximum Emax that driving voltage can be set is 100V, the peak frequency fmax that driving voltage can be set is 400Hz.
Control part 16 by control cables 17b, from condition switching part 26, receive and the size of driving voltage and the information of frequency dependence in, by voltage, apply cable 17a and to the generating unit 22 of pulsing, apply the driving voltage of the condition of switching part 26 appointments that satisfy condition.And control part 16 is controlled the starting of fluid supply mechanism 12 and is stopped by control cables 17c.
Foot switch 18 is switches of foot operation for operative doctor, by control cables 17d, is connected to control part 16.When operative doctor is connected foot switch 18, control part 16 when indication starts convection cell feed mechanism 12 supply fluids, applies driving voltage to pulsation generating unit 22.Then, being applied in the fluid of pulsing goes out from the peristome 20a high velocity jet of the front end of the fluid jet pipe 20 of handpiece 14.
Fig. 2 is the sectional view after a part that the inside of handpiece 14 forms is shown amplifies.The inside of the casing 24 of handpiece 14 is provided with the pulsation generating unit 22 that fluid to being supplied with by fluid supply mechanism 12 applies pulsation.Pulsation generating unit 22 comprises piezoelectric element 30, barrier film 32, the first housing 34, the second housing 36 and the 3rd housing 38.
In the inside of pulsation generating unit 22, by entrance stream 40, fluid chamber 42, outlet stream 44, form the stream that fluid that fluid supply mechanism 12 is supplied with passes through.In present embodiment, entrance stream 40 and outlet stream 44 are formed on the first housing 34, and fluid chamber 42 is formed between the first housing 34 and barrier film 32.Entrance stream 40 is connected with connection tube 19b, and outlet stream 44 is connected with fluid jet pipe 20.
Barrier film 32 is discoidal sheet metals, and its outer peripheral portion is sandwiched between the first housing 34 and the second housing 36 and is fixed.
Piezoelectric element 30 is actuators of the driving voltage work by being applied by control part 16.Piezoelectric element 30 is by the volume-variation of the fluid chamber 42 that makes between barrier film 32 and the first housing 34 to form, and changes the pressure of the fluid in fluid chamber 42.In present embodiment, piezoelectric element 30 is Piezoelektrisches mehrschichtelements, and barrier film 32 is fixed in one end, and the other end is fixed on the 3rd housing 38.
If the driving voltage being applied on piezoelectric element 30 increases, piezoelectric element 30 can extend, and barrier film 32 can be pressed Er Xiang fluid chamber 42 curvings by piezoelectric element 30.If barrier film 32Xiang fluid chamber 42 curvings, the volume of fluid chamber 42 can reduce, and the fluid in fluid chamber 42 can be forced out fluid chamber 42.In present embodiment, the internal diameter of outlet stream 44 is larger than the internal diameter of entrance stream 40.
That is to say, the inertia (inertance) of outlet stream 44 is less than the inertia of entrance stream 40, and therefore, the fluid in fluid chamber 42 is forced out fluid chamber 42 by outlet stream 44.
On the other hand, if the driving voltage being applied on piezoelectric element 30 reduces, piezoelectric element 30 can dwindle, and the volume of fluid chamber 42 increases, and fluid is conducted to fluid chamber 42 from entrance stream 40.
Because the driving voltage being applied on piezoelectric element 30 is for example, repeat to connect (maximum voltage) and turn-off (0V) with altofrequency (400Hz), therefore, the volume of fluid chamber 42 also repeatedly expands and dwindles, thereby convection cell applies pulsation.The fluid extruding from fluid chamber 42 is by the front end nozzle 20a(peristome 20a from fluid jet pipe 20) eject.
Fig. 3 is the key diagram of an example that the waveform of the driving voltage that piezoelectric element 30 is applied is shown.In Fig. 3, transverse axis express time, the longitudinal axis represents driving voltage.Between the rising stage that the one-period of the waveform of driving voltage is increased by voltage, between the decrement phase that reduces of voltage and do not execute between alive resting stage and form.
In present embodiment, the waveform between the rising stage of driving voltage is the waveform in 1/2 cycle of the SIN waveform of skew and phase deviation-90 degree in positive voltage direction.Waveform between the decrement phase of driving voltage is the waveform in 1/2 cycle of the SIN waveform of skew and phase deviation+90 degree in positive voltage direction.And the cycle of the SIN waveform of the period ratio of the SIN waveform between decrement phase between the rising stage is larger.
In present embodiment, when the size of driving voltage changes due to condition switching part 26, the maximum of the waveform shown in Fig. 3 also can change.And when the frequency of driving voltage changes due to condition switching part 26, the waveform between the rising stage and between decrement phase is constant, and length between resting stage can change.
Fig. 4 is the key diagram that the corresponding relation between the waveform of driving voltage and the deformation state of barrier film 32 is shown.In addition, in Fig. 4, between piezoelectric element 30 and barrier film 32, be provided with reinforcement feature 51.Between resting stage (a), owing to not applying driving voltage, piezoelectric element 30 can not extend, and barrier film 32 can be not crooked.Between the rising stage (b), because driving voltage increases, piezoelectric element 30 extends, barrier film 32Xiang fluid chamber 42 curvings, and the volume of fluid chamber 42 reduces.
In the timing shown in (c), because driving voltage is maximum, therefore, the length of piezoelectric element 30 also becomes maximum, and the volume of fluid chamber 42 becomes minimum.Between decrement phase (d) because driving voltage reduces, piezoelectric element 30 starts to recover original size, the volume of fluid chamber 42 also starts to recover original size.Between resting stage (e), owing to not applying driving voltage, piezoelectric element 30 returns to original size, and the volume of fluid chamber 42 also returns to original size.By repeating a series of actions shown in (a) to (e), the fluid in fluid chamber 42 is pressed out in fluid jet pipe 20.
(A) of Fig. 5, (B) of Fig. 5 are the key diagrams of the volume-variation of schematically illustrated fluid chamber 42.Wherein, Fig. 5 (A) do not show piezoelectric element 30 do not applied to driving voltage, and the volume of fluid chamber 42 is maximum state.It is maximum that (B) of Fig. 5 shows the driving voltage that piezoelectric element 30 is applied, and the volume of fluid chamber 42 is minimum state.And, in Fig. 5 (B) the region R of hatching be illustrated in driving voltage one-period during in the volume of the fluid chamber 42 that changes., region R represent driving voltage one-period during the volume of the fluid got rid of of Zhong Cong fluid chamber 42.The volume of the fluid of in this manual, Zhong Cong fluid chamber during the one-period of driving voltage 42 being got rid of is called excluded volume.At Fig. 5 (A),, in the schematic diagram shown in Fig. 5 (B), the product of the length that sectional area and the piezoelectric element 30 of excluded volume by fluid chamber 42 extends is tried to achieve.
In present embodiment, the excluded volume while piezoelectric element 30 being driven the maximum driving voltage Emax that can set by condition switching part 26 is defined as V1(ml).And, the maximum frequency that can set by condition switching part 26 is defined as to fmax(Hz).So, when piezoelectric element 30 being driven according to the frequency f max of maximum driving voltage Emax and maximum, the volume Vf(ml of the fluid of second Nei Cong fluid chamber 42 extrusion) as follows:
Vf＝V1×fmax
Yet, in fact, during the one-period of driving voltage in, compare excluded volume V1, have more fluid to eject from fluid jet pipe 20 as pulsating flow.Below, this phenomenon is described.
Fig. 6 is the schematically illustrated key diagram ejecting from fluid jet pipe 20 over the state of the fluid of the amount of excluded volume V1.As shown in Figure 6, once piezoelectric element 30 drives, the pulsating flow of droplet-like ejects from fluid jet pipe 20, and the drop of striated (streak-like) is being close to the drop spraying and is discharging from fluid jet pipe 20.This is the inertia effect due to fluid, and the fluid in fluid jet pipe 20 is pulled to the cause on the drop of injection.Consequently, when by maximum drive voltage Emax and peak frequency fmax driving pressure electric device 30, the fluid that surpasses the volume of above-mentioned excluded volume V1 ejects from fluid jet pipe 20 as pulsating flow.
Therefore, if fluid supply mechanism 12 is with Vf(ml/s) the flow fluid that carries out fluid chamber 42 supply with, when by maximum drive voltage Emax and peak frequency fmax driving pressure electric device 30, fluid can be not enough, thereby can not spray suitable pulsating flow.
Therefore,, in present embodiment, fluid supply mechanism 12 is to surpass Vf(ml/s) regulation flow supply flow body.Therefore, even by maximum drive voltage Emax and peak frequency fmax driving pressure electric device 30 in the situation that, also can suppression fluid not enough.
Particularly, when the once driving due to piezoelectric element 30 makes V1(ml) fluid of volume is when be forced out from fluid chamber 42, due to the inertia effect of fluid, suppose and V1(ml) volume of the fluid (drop of striated) that is jointly ejected of the fluid (drop) of volume is V2(ml).At this moment, the fluid supply mechanism 12 of present embodiment is to be more than or equal to (V1+V2) * fmax(ml/s) regulation flow supply flow body.In this way, Ke Xiang fluid chamber 42 supplies with the fluid of the desired flow of the fluid of considering that the inertia effect because of fluid ejects, and can suppression fluid not enough.
And, in present embodiment, even in the situation that the size of driving voltage and frequency are changed by condition switching part 26, also can surpass Vf(ml/s) regulation flow supply flow body.Therefore, even in the situation that driving voltage is little or the frequency of driving voltage is little, due to the amount of the fluid flow ejecting from fluid jet pipe 20 for regulation, therefore, also can be to using the operative doctor of fluid ejection apparatus 100 that stable use sense is provided.In addition, when driving voltage is changed into little value, or while changing into little frequency, by the fluid of oversupply, can from fluid jet pipe 20, be discharged as the Continuous Flow without pulsation.
And, verified: the volume V2 of the fluid (drop of striated) ejecting because of the inertia effect of fluid is less than excluded volume V1.Therefore, by once driving of piezoelectric element 30, be used as not enough V1 * 2.0 of volume (V1+V2) of the fluid that pulsating flow ejects.Therefore, the fluid supply mechanism 12 of present embodiment is with not enough V1 * 2.0 * fmax(ml/s) regulation flow fluid is supplied with to fluid chamber 42.Therefore, according to present embodiment, the phenomenon that superfluous fluid is supplied to fluid chamber 42 can be inhibited, and therefore, can suppress excessively to discharge without the Continuous Flow of pulsation from fluid jet pipe 20.Result is, can reduce the amount of used fluid, reduces and is trapped in the amount for the treatment of target fluid with it simultaneously, and guarantee good surgical field of view.
So, according to present embodiment, due to surpass Vf(ml/s) regulation flow supply flow body, therefore, even by maximum drive voltage Emax and peak frequency fmax driving pressure electric device 30 in the situation that, also the fluid in can suppression fluid chamber 42 is not enough, simultaneously to using the operative doctor of fluid ejection apparatus 100 that stable use sense is provided.
In addition, in actual fluid supply mechanism 12, even in the situation that supplying with fluid with " regulation " flow, it is very difficult accurately keeping regulation flow, and ± 10% variation occurs sometimes.Therefore, " regulation " in this description, also comprises the situation of follow ± 10% variation.And, because fluid supply mechanism 12 is roller pump or plunger displacement pump etc., therefore, even in the situation that follow the instantaneous variation of flow, as long as the flow that average flow is regulation in macroscopical time cycle can not damage effect of the present invention.
B. experimental example
In this experimental example, the supply flow rate of the fluid being provided by fluid supply mechanism 12 is provided one side, and one side is observed the pulsating flow ejecting from fluid jet pipe 20, and obtains the suitable supply flow rate of fluid.Then, the relative excluded volume V1 of the volume V2 accounting of the fluid (drop of striated) that the inertia effect because of fluid ejects is discussed how many.In addition, the supply flow rate of so-called fluid is suitable state, refers to when ejecting suitable pulsating flow, does not occur the state of unwanted Continuous Flow between pulsating flow and pulsating flow.
Do not need the reason of Continuous Flow to be, the pressure that Continuous Flow is only produced by fluid supply mechanism 12 extrudes, and therefore, the incision of affected part or excision etc. is not almost had to help.And if there is Continuous Flow, the fluid that remains in affected part will increase, surgical field of view meeting stenosis is narrow.
The condition of this experimental example is as follows:
Maximum drive voltage Emax:100V
Peak frequency fmax:400Hz
The maximum displacement of piezoelectric element while being applied in maximum drive voltage Emax: 10 μ m
The diameter of fluid chamber: 6mm
The sectional area of fluid chamber: 2.83 * 10
﹣ 5m
2
According to above condition, excluded volume V1 is as follows:
Excluded volume V1:2.83 * 10
﹣ 10m
3
And excluded volume per minute is as shown in the formula shown in (1):
V1 * fmax * 60=6.79ml/ divides ... (1)
Fig. 7 be illustrate pulsating flow spray moment chronophotograph key diagram.Fig. 7 shows few, the suitable and many situations of supply flow rate of fluid.As shown in Figure 7, when the supply flow rate of fluid lacks, owing to be filled in fluid jet pipe 20 at fluid before, the fluid in fluid jet pipe 20 can be forced out, and therefore, the pulsating flow ejecting will weaken.On the other hand, when the supply flow rate of fluid is many, before being about to that pulsating flow occurs, can there is Continuous Flow, thereby produce the very fast pulsating flow of speed below from this Continuous Flow.In addition, because the fluid in fluid jet pipe 20 was extruded by moment, therefore, the speed of pulsating flow is faster than the speed of Continuous Flow.
When the supply flow rate of fluid is just right, can there is not unwanted Continuous Flow, but pulsating flow occurs off and on.Particularly, after fluid is filled in fluid jet pipe 20, the fluid in fluid jet pipe 20 was extruded by moment, thereby fierce pulsating flow occurs.Then, in fluid is filled in fluid jet pipe 20 again, can there is not unwanted Continuous Flow, and after fluid is filled in fluid jet pipe 20, pulsating flow occur again.
Known by above-mentioned experiment, the suitable supply flow rate of fluid is 6.84ml/ minute.
Therefore, obtain following formula (2):
(V1+V2) * fmax * 60=6.84ml/ minute ... (2)
By formula (2), deduct formula (1), obtain following formula (3):
V2 * fmax * 60=0.05ml/ minute ... (3)
Relation by between formula (1) and formula (3) derivation V2 and V1, obtains following formula (4):
V2=V1×0.007…（4）
From the above, in the condition of this experimental example, the volume V2 of the fluid (drop of striated) spraying due to the inertia effect of fluid is 0.007 times of left and right of excluded volume V1.But, the ratio of V1 and V2 can because of the formation of fluid ejection apparatus 100 and the character of fluid different.Therefore, the ratio of V1 and V2, preferably according to the character of the formation of fluid ejection apparatus 100 and fluid, is suitably set.
C. variation:
In addition, this explanation is not limited in above-mentioned embodiment or embodiment, only otherwise depart from the aim that claim scope is recorded, can have other various embodiments, for example, also can be out of shape as follows.
Variation 1:
In the above-described embodiment, fluid ejection apparatus 100 is used as armarium.And in variation, other device that fluid ejection apparatus 100 also can be used as beyond armarium is used.For example, fluid ejection apparatus 100 also can be used as by sprayed fluid is aimed to object, thereby removes the cleaning device of the dirt of object; Or describe the drawing apparatus of word and picture as utilizing the fluid spraying.
Variation 2:
In the above-described embodiment, use liquid as the fluid ejecting from fluid ejection apparatus 100.And in variation, also can use gas as the fluid ejecting from fluid ejection apparatus 100.
Variation 3:
In the above-described embodiment, the magnitude range of the driving voltage that can set is 0V～100V, and the frequency range of the driving voltage that can set is 100Hz～400Hz.And on the other hand, in variation, the frequency range of the magnitude range of the driving voltage that can set and the driving voltage that can set can be also above-mentioned scope in addition.The frequency range of the driving voltage that for example, can set can be also 100Hz～1000Hz.
Variation 4:
In the above-described embodiment, excluded volume V1 can try to achieve according to the product between the sectional area of fluid chamber 42 and the maximum displacement of piezoelectric element 30.Yet strictly speaking, excluded volume V1 preferably equals the variable of the volume of real fluid chamber 42.Therefore,, when for example piezoelectric element 30 extends, when the internal pressure of fluid chamber 42 increases, preferably also should consider, because this pressure causes piezoelectric element 30, the part that strain is shunk occurs.And, the shape in the time of preferably also should considering barrier film 32 distortion.And, if the piezoelectric constant of known piezoelectric element 30 so, also can be tried to achieve according to piezoelectric constant and driving voltage the displacement of piezoelectric element 30.
Variation 5:
Above-mentioned embodiment adopts a kind of structure, that is:, when the driving voltage on being applied to piezoelectric element 30 increases, the volume of fluid chamber 42 reduces.And on the other hand, variation can adopt such structure, that is:, when the driving voltage on being applied to piezoelectric element 30 increases, the volume of fluid chamber 42 increases.
Variation 6:
In above-mentioned embodiment, condition switching part 26 is arranged in handpiece 14.And in variation, condition switching part 26 also can be arranged on other position beyond handpiece 14.For example, condition switching part 26 also can be arranged on control part 16.
Variation 7:
In above-mentioned embodiment, use piezoelectric element as pulsation generating unit 22.And in variation 7, also can use bubble generator as pulsation generating unit.Bubble generator also can be used such as heater and laser irradiation device etc.As bubble generator, so long as the fluid of heating in fluid chamber bubble is occurred, and pass through the device of the fluid in the expansion-injection fluid chamber of occurred bubble, all can use.
In this case, control part is controlled bubble generator and is made it periodically produce bubble, the peak frequency that control part produces bubble by bubble generator is fmax(Hz), when the variable quantity of the volume of the above-mentioned fluid chamber of the bubble that makes to produce by bubble generator when maximum is V1(ml) time, fluid supply unit also can surpass V1 * fmax(ml/s) afore mentioned rules flow supply with above-mentioned fluid.
Variation 7:
In the above-described embodiment, also can utilize hardware to realize the part in the function realizing by software, or also can utilize software to realize by the part in hard-wired function.
The present invention is not limited only to above-mentioned embodiment, embodiment and variation, only otherwise depart from the aim of interest field, can have various formations.For example, for part or all problem in addressing the above problem, or in order to reach part or all effect in above-mentioned effect, corresponding to the technical characterictic in embodiment, embodiment and the variation of the technical characterictic in each mode of recording in summary of the invention, can suitably substitute, combine.And, as long as its technical characterictic is not illustrated as content necessary in this description, can suitably delete.
Symbol description
10, fluid container 12, fluid supply mechanism
14, handpiece 16, control part
17a, voltage apply cable 17b, control cables
17c, control cables 17d, control cables
18, foot switch 19a, connection tube
19b, connection tube 20, fluid jet pipe
20a, nozzle (peristome) 22, pulsation generating unit
24, casing 26, condition switching part
30, piezoelectric element 32, barrier film
34, the first housing 36, the second housing
38, the 3rd housing 40, entrance stream
42, fluid chamber 44, outlet stream
51, reinforcement feature.
Claims (5)
1. a fluid ejection apparatus for jet fluid, comprising:
Playpipe, it sprays described fluid;
Fluid chamber, it is communicated to described playpipe;
Fluid supply unit, it supplies with described fluid with regulation flow to described fluid chamber;
Pulsation generating unit, it makes the fluid in described fluid chamber eject from described playpipe;
And
Control part, its control described pulsation generating unit action so that fluid periodically from described playpipe, eject,
When described control part makes the peak frequency of fluid jet, be fmax, when the variable quantity of the volume of described fluid chamber when described control part makes described pulsation generating unit action is V1, described fluid supply unit is supplied with described fluid to surpass the described regulation flow of V1 * fmax,
Wherein, the unit of described fmax is Hz, and the unit of described V1 is ml, and the unit of described V1 * fmax is ml/s.
2. fluid ejection apparatus according to claim 1, wherein, described fluid supply unit is supplied with described fluid with the described regulation flow of not enough V1 * 2.0 * fmax.
3. fluid ejection apparatus according to claim 1 and 2, wherein, when the fluid of V1 volume ejects from described injection peristome by the once driving of described pulsation generating unit, if while being V2 due to the fluid volume ejecting from described injection peristome together with the inertia effect of fluid and the described fluid of V1 volume, described fluid supply unit is supplied with described fluid to be more than or equal to the described regulation flow of (V1+V2) * fmax, wherein, the unit of described V2 is ml.
4. fluid ejection apparatus according to claim 3, wherein,
Described V2 is V1 * 0.007.
5. one kind has used claim 1 to the armarium of the fluid ejection apparatus described in any one in claim 4.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP2013-067718 | 2013-03-28 | ||
| JP2013067718A JP6186798B2 (en) | 2013-03-28 | 2013-03-28 | Fluid ejecting apparatus and medical device |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CN104068914A true CN104068914A (en) | 2014-10-01 |
Family
ID=50382335
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201410120713.1A Pending CN104068914A (en) | 2013-03-28 | 2014-03-27 | Fluid ejection device and medical apparatus |
Country Status (4)
| Country | Link |
|---|---|
| US (1) | US9737327B2 (en) |
| EP (1) | EP2783645B1 (en) |
| JP (1) | JP6186798B2 (en) |
| CN (1) | CN104068914A (en) |
Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106460824A (en) * | 2014-07-11 | 2017-02-22 | 精工爱普生株式会社 | Liquid injection control device, liquid injection system, and control method |
| CN113649238A (en) * | 2021-09-06 | 2021-11-16 | 业成科技（成都）有限公司 | Fluid control device and dispensing device thereof |
Families Citing this family (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JP2015058240A (en) * | 2013-09-20 | 2015-03-30 | セイコーエプソン株式会社 | Medical device system and liquid supply device |
| JP2016120024A (en) * | 2014-12-24 | 2016-07-07 | セイコーエプソン株式会社 | Liquid injection control device, and liquid injection system and control method |
| JP2016120023A (en) | 2014-12-24 | 2016-07-07 | セイコーエプソン株式会社 | Liquid injection control device, and liquid injection system and control method |
| WO2021080567A1 (en) * | 2019-10-22 | 2021-04-29 | Hewlett-Packard Development Company, L.P. | Fluidic die with a suppressible clock circuit |
| JP7443845B2 (en) * | 2020-03-16 | 2024-03-06 | セイコーエプソン株式会社 | liquid injection device |
Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2119203U (en) * | 1992-04-15 | 1992-10-21 | 第二汽车制造厂 | Double-orifice water jet cutting scalpel and device |
| US20050147502A1 (en) * | 2003-10-24 | 2005-07-07 | Kunihiko Takagi | Method of driving pump |
| CN101658439A (en) * | 2008-08-27 | 2010-03-03 | 精工爱普生株式会社 | Pulsation generating mechanism, connecting flow channel tube, and fluid ejecting apparatus |
| US20100069937A1 (en) * | 2008-09-16 | 2010-03-18 | Seiko Epson Corporation | Fluid jet device, drive device of fluid jet device, surgical instrument, and method of driving fluid jet device |
Family Cites Families (22)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPH06277283A (en) | 1993-03-30 | 1994-10-04 | Sharp Corp | Infusion device |
| DK1248660T3 (en) | 2000-01-21 | 2012-07-23 | Medtronic Minimed Inc | Microprocessor controlled outpatient medical device with handheld communication device |
| US6589229B1 (en) | 2000-07-31 | 2003-07-08 | Becton, Dickinson And Company | Wearable, self-contained drug infusion device |
| JP2003071448A (en) | 2001-08-31 | 2003-03-11 | Mikuni Corp | Electrolytic water maker |
| JP2003180826A (en) | 2001-12-17 | 2003-07-02 | Terumo Corp | Medicinal liquid infusion apparatus |
| JP2003180827A (en) | 2001-12-17 | 2003-07-02 | Terumo Corp | Medicinal liquid infusion apparatus |
| JP4095374B2 (en) | 2002-08-27 | 2008-06-04 | ペンタックス株式会社 | Endoscope water supply device |
| JP2004309163A (en) | 2003-04-02 | 2004-11-04 | Yaskawa Electric Corp | Liquid feeding module, liquid feeding apparatus, and driving method therefor |
| JP4444640B2 (en) | 2003-12-15 | 2010-03-31 | 川澄化学工業株式会社 | Infusion pump device |
| JP2005192807A (en) | 2004-01-07 | 2005-07-21 | Cyber Firm Inc | Somatic condition regulating system |
| JP2006136376A (en) | 2004-11-10 | 2006-06-01 | K & Y:Kk | Disposable infusion device system |
| JP5082049B2 (en) | 2006-09-26 | 2012-11-28 | セイコーエプソン株式会社 | Fluid ejecting apparatus and surgical tool |
| JP4933911B2 (en) | 2007-02-02 | 2012-05-16 | 学校法人日本医科大学 | Ultrasound surgical device |
| JP5115088B2 (en) | 2007-08-10 | 2013-01-09 | セイコーエプソン株式会社 | Surgical tool |
| JP2009055958A (en) | 2007-08-30 | 2009-03-19 | Terumo Corp | Medical solution cartridge and medical solution injection device using the same |
| JP2009078041A (en) | 2007-09-27 | 2009-04-16 | Terumo Corp | Medical solution cartridge and medical solution injection device using the same |
| JP4788809B2 (en) | 2009-08-17 | 2011-10-05 | セイコーエプソン株式会社 | Fluid injection method |
| JP2011143145A (en) * | 2010-01-18 | 2011-07-28 | Seiko Epson Corp | Liquid-jet device |
| JP2011160868A (en) | 2010-02-05 | 2011-08-25 | Ricoh Co Ltd | Flow rate control apparatus and pump apparatus |
| JP2011177411A (en) | 2010-03-03 | 2011-09-15 | Ricoh Co Ltd | Infusion volume adjusting device, method for adjusting infusion volume, infusion system, and program |
| JP2012035101A (en) | 2011-10-17 | 2012-02-23 | Nippon Medical School | Ultrasonic surgical instrument |
| JP5408324B2 (en) | 2012-10-15 | 2014-02-05 | セイコーエプソン株式会社 | Fluid ejecting apparatus and medical device |
-
2013
- 2013-03-28 JP JP2013067718A patent/JP6186798B2/en active Active
-
2014
- 2014-03-27 CN CN201410120713.1A patent/CN104068914A/en active Pending
- 2014-03-27 US US14/227,374 patent/US9737327B2/en active Active
- 2014-03-27 EP EP14161974.2A patent/EP2783645B1/en active Active
Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN2119203U (en) * | 1992-04-15 | 1992-10-21 | 第二汽车制造厂 | Double-orifice water jet cutting scalpel and device |
| US20050147502A1 (en) * | 2003-10-24 | 2005-07-07 | Kunihiko Takagi | Method of driving pump |
| CN101658439A (en) * | 2008-08-27 | 2010-03-03 | 精工爱普生株式会社 | Pulsation generating mechanism, connecting flow channel tube, and fluid ejecting apparatus |
| US20100069937A1 (en) * | 2008-09-16 | 2010-03-18 | Seiko Epson Corporation | Fluid jet device, drive device of fluid jet device, surgical instrument, and method of driving fluid jet device |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN106460824A (en) * | 2014-07-11 | 2017-02-22 | 精工爱普生株式会社 | Liquid injection control device, liquid injection system, and control method |
| CN113649238A (en) * | 2021-09-06 | 2021-11-16 | 业成科技（成都）有限公司 | Fluid control device and dispensing device thereof |
| CN113649238B (en) * | 2021-09-06 | 2022-08-30 | 业成科技（成都）有限公司 | Fluid control device and dispensing device thereof |
Also Published As
| Publication number | Publication date |
|---|---|
| EP2783645B1 (en) | 2016-09-14 |
| EP2783645A1 (en) | 2014-10-01 |
| JP6186798B2 (en) | 2017-08-30 |
| JP2014190279A (en) | 2014-10-06 |
| US20140296895A1 (en) | 2014-10-02 |
| US9737327B2 (en) | 2017-08-22 |
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